Dynamic collimation for computed tomography

ABSTRACT

A collimator for a computed tomography imaging device can include first and second leaves positioned on and bounding opposing sides of a radiation delivery window. The first and second leaves can be movable to adjust at least one of a size or a location of the primary radiation delivery window relative a the radiation source in a direction non-parallel to an axis of rotation of the radiation source.

GOVERNMENT LICENSE RIGHTS

This invention was made with government support under grants R01EB007168 and R21 EB007236 awarded by the National Institutes of Health.The Government has certain rights to this invention.

FIELD

The subject technology relates generally to radiological devices andmethods and, in some embodiments, more particularly to devices andmethods for computed tomography (CT).

BACKGROUND

CT systems have included single-slice and multiple-slice detectors. CTsystems with multiple-slice detectors are, in particular, able scanlarge volumes of interest. Some large volumes are imagined by helical CTscanning. In helical scanning, the subject moves axially relative to aradiation beam such that the beam traverses a helical path through thesubject. Such scanning can be leveraged to quickly scan whole or largeportions of organs.

SUMMARY

As aspect of at least one embodiment disclosed herein includes therealization that high radiation dose of conventional perfusion CTimaging and the lack of standardized perfusion CT imaging protocolslimit the clinical potential of CT. Some embodiments disclosed hereinsignificantly reduce the x-ray dose of CT perfusion scans withoutsacrificing clinical accuracy. Some embodiments that significantlyreduce the x-ray dose of CT perfusion scans without sacrificing clinicalaccuracy, thereby expand use of perfusion CT as a diagnostic tool. Someembodiments of devices and methods for perfusion CT imaging can used fordiagnosis, treatment of diseases, or both. In various embodiments, aradiation dose delivered to a subject can be reduced by application ofany one of a transverse dynamic collimator, a grated collimator, anadaptive sampling algorithm, or an adaptive exposure algorithm, or acombination of some or all thereof. Some embodiments can be used forperfusion imaging of the kidneys, pancreas, liver, and heart.

Primarily due to concerns about the magnitude of radiation dosedelivered, perfusion CT imaging has not been used routinely in variousfields, including stroke assessment, oncology, and cardiac and kidneyfunction. In some embodiments, reduction of radiation dose delivered toa subject can permit application of perfusion CT to those applicationswherein dose is a limiting factor, e.g. cardiac perfusion. Although someembodiments are discussed herein with respect to perfusion. CT imaging,some embodiments can be used with other imaging. Similarly, althoughsome embodiments may provide particular benefits for perfusion CTimaging, various embodiments can provide advantages with other imaging.

The subject technology is illustrated, for example, according to variousaspects described below. Various examples of aspects of the subjecttechnology are described as numbered clauses (1, 2, 3, etc.) forconvenience. These are provided as examples and do not limit the subjecttechnology. It is noted that any of the dependent clauses may becombined in any combination, and placed into a respective independentclause, e.g., clause 1 or clause 55. The other clauses can be presentedin a similar manner.

1. A collimator for a computed x-ray tomography imaging device,comprising a first grating and a second grating positioned on opposingsides of a primary radiation delivery window, each of the first andsecond gratings comprising a plurality of attenuating members with aplurality of secondary radiation delivery windows extending betweenadjacent attenuating members of the first grating and the secondgrating, respectively.

2. The collimator of clause 1, wherein a width of each secondary windowsis less than a width of the primary window.

3. The collimator of clause 1, wherein a total area of each of theplurality of secondary windows is less than a total area of the primarywindow.

4. The collimator of clause 1, wherein a width of each secondary windowis proportional to a distance between the secondary window and theprimary window.

5. The collimator of clause 4, wherein the width of each secondarywindow is linearly proportional to the distance between the secondarywindow and the primary window.

6. The collimator of clause 4, wherein the width of each secondarywindow is positively proportional to the distance between the secondarywindow and the primary window.

7. The collimator of clause 1, wherein a width of each attenuatingmember is proportional to a distance between the attenuating member andthe primary window.

8. The collimator of clause 7, wherein the width of each attenuatingmember is linearly proportional to the distance between the attenuatingmember and the primary window.

9. The collimator of clause 7, wherein the width of each attenuatingmember is positively proportional to the distance between theattenuating member and the delivery window.

10. The collimator of clause 1, wherein the secondary windows compriseopen passages extending through the grating.

11. The collimator of clause 1, wherein the secondary windows comprisepanes of substantially radio-transmissive material.

12. The collimator of clause 1, wherein the attenuating members areoriented generally parallel to sides of the primary window.

13. The collimator of clause 1, wherein the secondary windows areoriented generally parallel to sides of the primary window.

14. The collimator of clause 1, wherein the first grating is movablerelative to the second grating.

15. The collimator of clause 14, wherein the first and second gratingsare independently movable.

16. The collimator of clause 1, wherein the attenuating members of thefirst grating are integrally formed with each other, and the attenuatingmembers of the second grating are integrally formed with each other.

17. The collimator of clause 16, wherein the attenuating members of thefirst grating are integrally formed with the attenuating members of thesecond grating.

18. A method of directing radiation during computed tomography (CT)imaging, comprising:

-   -   emitting x-ray radiation from a radiation source toward an        object;    -   passing a first portion of the radiation through a primary        window toward a target region in the object;    -   passing a second portion of the radiation through at least one        secondary window, on each of opposing sides of the primary        window, to corresponding regions in the object outside the        target region;    -   attenuating, between the primary and secondary windows, at least        a third portion of the radiation; and    -   generating CT image data based on the first and second portions        of the radiation.

19. The method of clause 18, further comprising rotating the radiationsource and the primary and secondary windows about an axis, and whereinradiation is passed through the primary window and the secondary windowswhile either (i) centers of the primary window and at least two of thesecondary windows lie in a plane non-parallel to the axis or (ii) aplane intersecting the centers and the axis is non-parallel to the axis.

20. The method of clause 18, further comprising rotating the radiationsource and the primary and secondary windows about an axis, andtranslating the secondary windows relative to the primary window in adirection non-parallel to the axis.

21. The method of clause 20, wherein the secondary windows aretranslated relative to the primary window during rotation of theradiation source.

22. The method of clause 21, wherein a first of the secondary windows istranslated independently of a second of the secondary windows on anopposing side of the primary window from the first of the secondarywindows.

23. The method of clause 18, wherein the attenuating comprises blockingpassage of at least the third portion of the radiation between theprimary and secondary windows.

24. A computed tomography device, comprising:

-   -   a gantry configured to rotate about an axis and comprising an        opening configured to accommodate an object;    -   a radiation source mounted to the gantry;    -   a collimator positioned between the radiation source and the        gantry opening, the collimator comprising first and second        leaves respectively bounding first and second opposing sides of        a radiation delivery window, the first leaf and the second leaf        being movable to adjust at least one of a size or a location of        the radiation delivery window relative to the radiation source        in a direction non-parallel to the axis.

25. The computed tomography device of clause 24, wherein the first leafis moveable independently of the second leaf.

26. The computed tomography device of clause 24, further comprisingthird and fourth leaves respectively bounding third and fourth opposingsides of the window and aligned with the window along the axis.

27. The computed tomography device of clause 26, wherein each of thefirst and second sides is substantially orthogonal to each of the thirdand fourth sides.

28. The computed tomography device of clause 24, wherein the collimatoris mounted within about 27 cm of the radiation source.

29. The computed tomography device of clause 24, wherein the collimatoris mounted within about 12 cm of the radiation source.

30. A computed tomography device, comprising:

-   -   a gantry configured to rotate about an axis and comprising an        opening configured to accommodate an object;    -   a radiation source mounted to the gantry;    -   a collimator positioned between the radiation source and the        gantry opening, the collimator comprising a first leaf and a        second leaf respectively bounding first and second opposing        sides of a radiation delivery window, the first leaf and the        second leaf being independently movable relative to the        radiation source in a direction non-parallel to the axis.

31. The device of clause 30, wherein the first leaf and the second leafare independently movable relative to the radiation source in adirection tangential to a circle (i) centered on the axis and (i)defining a plane that is not parallel to the axis.

32. The device of clause 31, wherein the first leaf is independentlymovable relative to the second leaf.

33. A method of radiologic imaging, comprising:

-   -   rotating, about an axis, a gantry carrying a radiation source;    -   emitting radiation from the radiation source toward an object        between a pair of leaves;    -   during rotation of the gantry, moving the pair of leaves        relative to the radiation source in a direction nonparallel to        the axis.

34. The method of clause 33, further comprising:

-   -   performing a preliminary scan of a object;    -   demarcating a region of interest in the object, based on the        preliminary scan, that is at least one of (i) non-concentric        with the axis or (ii) non-circular; and    -   controlling movement of the pair of leaves during rotation of        the gantry to adjust at least one of a location, relative to the        radiation source, or a dimension, of a radiation. delivery        window such that substantially only the region of interest is        exposed to radiation through the radiation delivery window.

35. The method of clause 34, further comprising directing radiationthrough a plurality of secondary windows, on opposing sides of theradiation delivery window, to regions in the object outside the regionof interest; and substantially blocking the passage of radiation towardthe object in regions between the radiation delivery window and thesecondary windows.

36. The method of clause 33, further comprising repositioning the objectsuch that a region of interest is located closer to the axis.

37. A method of contrast-enhanced computed tomography (CT) imaging,comprising:

-   -   (a) repeatedly scanning a target region at a frequency during a        session, the scanning comprising performing a CT scan by        emitting x-ray radiation toward the target region, the frequency        initially being a first rate;    -   (b) monitoring, during the session, an indicator of attenuation        of radiation by a contrast-enhanced first structure within the        target region;    -   (c) after detecting an increase of the attenuation, increasing        the frequency to a second rate; and    -   (d) after detecting a decrease in the attenuation after (c),        decreasing the frequency to a third rate.

38. The method of clause 37, further comprising generating arepresentation of a relationship between time and radiation attenuationby a second structure within the target region.

39. The method of clause 38, wherein the radiation attenuation by thesecond structure with respect to time represents an indicator ofvascular perfusion of the second structure.

40. The method of clause 37, further comprising monitoring of a rate ofchange of the attenuation.

41. The method of clause 40, wherein the frequency is increased to thesecond rate in response to detection of a decrease in a rate at whichthe attenuation is increasing.

42. The method of clause 41, further comprising beginning monitoring ofthe rate of change after detecting an increase of the attenuation to orbeyond a threshold.

43. The method of clause 42, wherein the threshold is about 35 HU.

44. The method of clause 42, wherein the threshold comprises a degree ofincrease in the attenuation compared to a value indicated by an initialscan.

45. The method of clause 40, further comprising decreasing the frequencybelow the third rate in response to detection of a decrease in a rate atwhich the attenuation is decreasing.

46. The method of clause 45, wherein decreasing the frequency below thethird rate comprises reducing the frequency with each successive scan.

47. The method of clause 46, wherein the frequency is approximatelyhalved with each successive scan.

48. The method of clause 37, wherein the frequency is reduced to thethird rate upon a first detection of a decrease in attenuation after(c).

49. The method of clause 37, wherein the first rate is one scanapproximately every two seconds.

50. The method of clause 37, wherein the second rate is one scanapproximately every second.

51. The method of clause 37, wherein the third rate is one scanapproximately every two seconds.

52. The method of clause 37, wherein the structure comprises at leastone of a heart chamber, an aorta, or another blood vessel.

53. The method of clause 37, further comprising terminating the scanningafter a predetermined period of time and performing a final scan at theend of the predetermined period.

54. The method of clause 37, further comprising terminating the scanningafter a predetermined period of time, and, if a remaining time between alatest scan and an end of the predetermined period is less than aninterval between the latest scan and an immediately preceding scan,performing (i) a penultimate scan at approximately half of the remainingtime after the latest scan and (ii) a final scan at the end of thepredetermined period.

55. A computer-implemented system for controlling contrast-enhancedcomputed tomography imaging, comprising:

-   -   an attenuation monitoring module configured to monitor, during        an imaging session, an indicator of attenuation of radiation by        a contrast-enhanced structure within a target region;    -   a scanning-frequency control module configured to (i) increase a        frequency of scanning from a first rate to a second rate after        detection of an increase of the attenuation, and (ii) decrease        the frequency to a third rate after detecting a decrease in        attenuation after increasing the frequency to the second rate.

56. The computer-implemented system of clause 55, wherein the monitoringmodule is further configured to monitor a rate of change of theattenuation.

57. The computer-implemented system of clause 56, wherein thescanning-frequency control module is further configured to increase thefrequency to the second rate in response to detection of a decrease in arate at which the attenuation is increasing.

58. The computer-implemented system of clause 56, wherein the monitoringmodule is further configured to begin monitoring of the rate of changeafter detection of compliance of the attenuation with a threshold.

59. The computer-implemented system of clause 58, wherein the thresholdis 35 HU.

60. The computer-implemented system of clause 58, wherein the thresholdis a degree of increase in the attenuation compared to a value indicatedby an initial scan.

61. The computer-implemented system of clause 55, further comprising aprocessing module configured to generate a representation of arelationship between time and radiation attenuation by a secondstructure within the target region.

62. The computer-implemented system of clause 61, wherein the radiationattenuation by the second structure with respect to time represents anindicator of vascular perfusion of the second structure.

63. The computer-implemented system of clause 55, wherein thescanning-frequency control module is further configured to decrease thefrequency below the third rate in response to detection of a decrease ina rate at which the attenuation is decreasing.

64. The computer-implemented system of clause 63, wherein thescanning-frequency control module is further configured to decrease thefrequency further below the third rate with each successive scan.

65. The computer-implemented system of clause 64, wherein thescanning-frequency control module is further configured to divide thefrequency by approximately two with each successive scan.

66. The computer-implemented system of clause 55, wherein thescanning-frequency control module is further configured to reduce thefrequency to the third rate upon a first detection of a decrease inattenuation after an increase to the second rate.

67. The computer-implemented system of clause 55, further comprising atermination module configured to terminate the scanning after apredetermined period of time and direct performance of a final scan atthe end of the predetermined period.

68. The computer-implemented system of clause 55, further comprising atermination module configured to terminate the scanning after apredetermined period of time, and, if a remaining time between a latestscan and an end of the predetermined period is less than an intervalbetween the latest scan and an immediately preceding scan, directperformance of (i) a penultimate scan at a half of the remaining timeafter the latest scan and (ii) a final scan at the end of thepredetermined period.

69. A computed tomography imaging system, comprising:

-   -   a gantry comprising an opening configured to accommodate an        object;    -   a radiation source mounted to the gantry;    -   a radiation detector mounted to the gantry opposite the        radiation source relative to the opening;    -   an attenuation monitoring module configured to monitor, during        an imaging session, an indicator of attenuation of radiation by        a contrast-enhanced structure within a target region;    -   a scanning-frequency control module configured to (i) increase a        frequency of scanning from a first rate to a second rate after        detection of an increase of the attenuation, and (ii) decrease        the frequency to a third rate after detecting a decrease in        attenuation after increasing the frequency to the second rate.

70. A method of computed tomography imaging, comprising:

-   -   repeatedly emitting x-ray radiation into a target region at a        frequency during a session;    -   monitoring, during the session, an indicator of attenuation of        radiation by a contrast-enhanced first structure within the        target region;    -   varying the frequency based on the attenuation.

71. The method of clause 70, wherein x-ray radiation is emitted at aminimum frequency when the attenuation is below a low threshold and at amaximum frequency when then attenuation is above a high threshold.

72. A method of contrast-enhanced computed tomography (CT) imaging,comprising:

-   -   (a) repeatedly scanning a target region during a session, the        scanning comprising performing a CT scan by emitting x-ray        radiation at an applied power toward the target region, the        applied power being a first power for a first scan;    -   (b) monitoring an indicator of attenuation of radiation by a        contrast-enhanced first structure within the target region; and    -   (c) selecting the applied power for each of a plurality of        scans, after a first scan, based on the attenuation indicated        from a preceding scan in the session.

73. The method of clause 72, wherein the first power is a maximum powerapplied during the session.

74. The method of clause 72, wherein the applied power is determined byselection of an applied current.

75. The method of clause 74, wherein the first applied current is about200 ma.

76. The method of clause 72, further comprising applying substantiallythe first applied power to individual scans until detection of anincrease of the attenuation to or beyond a threshold attenuationmagnitude.

77. The method of clause 76, wherein the threshold attenuation magnitudeis about 35 HU.

78. The method of clause 76, wherein the threshold attenuation magnitudeis a predetermined proportion of the attenuation determined from aninitial scan.

79. The method of clause 76, wherein the threshold attenuation magnitudeis a predetermined number of Hounsfield Units greater than theattenuation determined from an initial scan.

80. The method of clause 72, wherein the applied power is selected bymultiplying a maximum current by an exponential function based on theattenuation determined from the preceding scan.

81. The method of clause 80, wherein the exponential function yields avalue that is (i) greater than a minimum allowable current divided by amaximum allowable current, and (ii) less than 1.

82. The method of clause 80, wherein the exponential function is afunction F determined byF=e ^(C·) ^((TH−ΔHU)) ^(/) TH

-   -   wherein TH is a threshold attenuation magnitude and ΔHU is equal        to a difference in magnitude, in Hounsfield Units, between the        attenuation determined from a preceding scan and a baseline        attenuation.

83. The method of clause 82, wherein the preceding scan is a scanimmediately prior to a scan performed according the applied power asdetermined by the function F.

84. The method of clause 82, wherein the baseline attenuation is amagnitude of the attenuation indicated based on the initial scan.

85. The method of clause 82, wherein C is selected such that, when thefunction is applied, an applied current for a next scan is about a tenthof the maximum allowable current when the attenuation of the precedingscan is about ten times above the threshold attenuation magnitude.

86. The method of clause 82, wherein C is about 0.25.

87. The method of clause 82, further comprising selecting an appliedpower corresponding to a minimum allowable current for each scan forwhich the function F indicates, based on the attenuation indicated by apreceding scan, a current less than the minimum allowable current.

88. A computer-implemented system for controlling contrast-enhancedcomputed tomography imaging, comprising:

-   -   an attenuation monitoring module configured to monitor, during        an imaging session, an indicator of attenuation of radiation by        a contrast-enhanced structure within a target region;    -   a power control module configured to select an applied power for        each of a plurality of scans based on the attenuation detected        from a preceding scan.

89. The computer-implemented system of clause 88, wherein the powercontrol module is further configured to direct application of a maximumpower applied during the session in a first scan.

90. The computer-implemented system of clause 88, wherein the powercontrol module is further configured to apply substantially the sameamount of power to individual scans until detection of an increase ofthe attenuation to or beyond a threshold attenuation magnitude.

91. The computer-implemented system of clause 88, wherein the powercontrol module is further configured to select the applied power bymultiplying a maximum current by an exponential function.

92. A computed tomography imaging system, comprising:

-   -   a gantry comprising an opening configured to accommodate an        object;    -   a radiation source mounted to the gantry;    -   a radiation detector mounted to the gantry opposite the        radiation source relative to the opening;    -   an attenuation monitoring module configured to monitor, during        an imaging session, an indicator of attenuation of radiation by        a contrast-enhanced structure within a target region;    -   a power control module configured to select an applied power for        each of a plurality of scans based on the attenuation detected        from a preceding scan.

93. A method of computed tomography imaging, comprising:

-   -   repeatedly emitting x-ray radiation into a target region, each        emission having an input power;    -   monitoring an attenuation of radiation through a structure        within the target region;    -   varying the input power based on the attenuation.

94. The method of clause 93, further comprising applying a minimum inputpower when the attenuation is above a high threshold and applying amaximum input power when then attenuation is below a low threshold.

Additional features and advantages of the subject technology will be setforth in the description below, and in part will be apparent from thedescription, or may be learned by practice of the subject technology.The advantages of the subject technology will be realized and attainedby the structure particularly pointed out in the written description andclaims hereof as well as the appended drawings.

It is to be understood that both the foregoing general description andthe following detailed description are exemplary and explanatory and areintended to provide further explanation of the subject technology asclaimed.

BRIEF DESCRIPTION OF THE DRAWINGS

The accompanying drawings, which are included to provide furtherunderstanding of the subject technology and are incorporated in andconstitute a part of this specification, illustrate aspects of thesubject technology and together with the description serve to explainthe principles of the subject technology.

FIG. 1 illustrates an exemplifying CT imaging system according to anembodiment.

FIG. 2 is an enlarged perspective view of a radiation source mounted toa rotatable gantry and a transverse collimator positioned along a pathof radiation emission.

FIG. 3 illustrates limitation of radiation exposure to a region ofinterest at multiple positions of a dynamic transverse collimatoraccording to an embodiment.

FIG. 4 illustrates the outline of volume of interest (VOI) correspondingto a heart.

FIG. 5 schematically illustrates an exemplifying embodiment of a dynamiccollimator according to an embodiment.

FIG. 6 illustrates a perspective view of an exemplifying embodiment of agrated collimator according to an embodiment.

FIG. 7 illustrates an exemplifying embodiment of a dynamic gratedcollimator according to an embodiment.

FIG. 8 illustrates a region of interest within a field of view.

FIG. 9 illustrates an example of an image generated based on a scanusing a grated collimator, with no correction applied.

FIG. 10 is a schematic diagram of transverse dynamic collimator geometryaccording to an embodiment.

FIGS. 11 and 12 are schematic diagrams of dynamic axial collimatorleaves.

FIGS. 13-15 are plots of the velocities (in cm/s) for a transversecollimator leaf.

FIG. 16 is a plot of the velocities (in cm/s) for axial collimatorleaves.

FIG. 17 shows the three cross-sections of a subject, each with anindicated target region of interest.

FIG. 18 illustrates geometry for a ray at angle α directly exposing theskin, emanating from the x-ray source located at angle θ.

FIG. 19 illustrates another geometry for a ray at angle α indirectlyexposing the skin, emanating from the x-ray source located at angle θ.

FIG. 20 illustrates geometry for a ray at angle α exposing the center ofthe target ROI.

FIG. 21 shows a central kidney cross-section showing ellipses definingthe outline of the body and target ROI including both kidneys withreference lines.

FIGS. 22A-E show five equally-spaced kidney cross-sections showing bodyoutlines and target ROIs including both kidneys with reference lines.

FIG. 23 illustrates a method of contrast-enhanced computed tomography(CT) imaging.

FIG. 24 schematically illustrates a curve representing a magnitude ofradiation attenuation (vertical axis) by a contrast-enhanced structureover time (horizontal axis).

FIG. 25 is an exemplifying plot a of magnitudes of radiation attenuation(vertical axis) by various contrast-enhanced structures over time(horizontal axis), and shows sampling rates and intervals according toan exemplifying embodiment.

FIG. 26 illustrates a method of contrast-enhanced computed tomography(CT) imaging.

FIG. 27 is an exemplifying plot a of magnitudes of radiation attenuation(vertical axis) by various contrast-enhanced structures over time(horizontal axis), and indicates a current magnitude for a plurality ofscans.

FIG. 28 is an exemplifying plot a of magnitudes of radiation attenuation(vertical axis) by various contrast-enhanced structures over time(horizontal axis), and indicates a current magnitude for a plurality ofscans.

FIG. 29 is an image corresponding to a scan from a series of scansindicated in FIG. 28.

FIG. 30 is a diagram illustrating an exemplifying system, including aprocessor and other internal components, according to an aspect of thesubject technology

FIG. 31 is a diagram illustrating an exemplary communication between aserver and a client machine according to an aspect of the subjecttechnology.

DETAILED DESCRIPTION

In the following detailed description, numerous specific details are setforth to provide a full understanding of the subject technology. It willbe apparent, however, to one ordinarily skilled in the art that thesubject technology may be practiced without some of these specificdetails. In other instances, well-known structures and techniques havenot been shown in detail so as not to obscure the subject technology.

A phrase such as “an aspect” does not imply that such aspect isessential to the subject technology or that such aspect applies to allconfigurations of the subject technology. A disclosure relating to anaspect may apply to all configurations, or one or more configurations.An aspect may provide one or more examples of the disclosure. A phrasesuch as “an aspect” may refer to one or more aspects and vice versa. Aphrase such as “an embodiment” does not imply that such embodiment isessential to the subject technology or that such embodiment applies toall configurations of the subject technology. A disclosure relating toan embodiment may apply to all embodiments, or one or more embodiments.An embodiment may provide one or more examples of the disclosure. Aphrase such “an embodiment” may refer to one or more embodiments andvice versa. A phrase such as “a configuration” does not imply that suchconfiguration is essential to the subject technology or that suchconfiguration applies to all configurations of the subject technology. Adisclosure relating to a configuration may apply to all configurations,or one or more configurations. A configuration may provide one or moreexamples of the disclosure. A phrase such as “a configuration” may referto one or more configurations and vice versa.

Although many features, aspects and embodiments are described herein orshown in the accompanying drawings in the context of CT, the disclosedtechnology can also be applied in other imaging systems and methods,other medical scenarios, or other image data acquisition or processingtechniques.

Primarily due to concerns about the magnitude of radiation dosedelivered, perfusion CT imaging has not been used routinely in variousfields, including stroke assessment, oncology, and cardiac and kidneyfunction. In some embodiments, reduction of radiation dose delivered toa subject can permit application of perfusion CT to those applicationswherein dose is a limiting factor, e.g. cardiac perfusion. In someembodiments, perfusion CT can be applied to stroke assessment, oncology,and assessment of cardiac and kidney function. In various embodiments, aradiation dose delivered to a subject can be reduced by application of atransverse dynamic collimator, a grated collimator, an adaptive samplingalgorithm, an adaptive exposure algorithm, or a combination thereof. Insome embodiments, the radiation dose of perfusion CT can besignificantly reduced without impacting diagnostic accuracy

During a helical CT scan, an X-ray source generates a cone (or wedge)beam of radiation that moves relative to the patient. Portions of thecone beam of radiation may not pass through the volume to bereconstructed. While this extra radiation may have little adverse effecton the clinical use of the reconstructed image, it can subject thepatient to more radiation than is necessary. Accordingly, variousembodiments described herein relate to replacing a conventionalcollimator with a dynamically transversely adjustable collimator. Thecollimator can be actuated by an electromechanical servo system. Theimaging system can comprise a control (e.g., an electronic control) thatis responsive to sensor(s) for sensing the axial and rotational positionof the X-ray source relative to a volume of interest. As the X-raysource rotates about an axis, the collimator is adjusted (i) to adjustthe width, location, or both of the radiation beam so that radiation isprimarily allowed to pass through the volume of interest and (ii) toblock some or all of the rays of radiation that will not intersect thevolume of interest.

FIG. 1 illustrates an exemplifying CT imaging system 100 including a CTscanner 102 with a gantry portion 104, a radiation source unit 112, adetector 124, and a couch or support 126. The gantry portion 104 cancomprise a gantry opening 106 and can rotate about an examination region108. The rotating gantry portion 104 can support the radiation sourceunit 112 and the detector 124.

The radiation source unit 112 can be an x-ray source, such as an X-raytube, for example. The radiation source can emit a radiation beam. Theradiation beam can be a cone beam, wedge beam, or other desirable beamshape. The beam can be collimated to have a generally conical geometryin some embodiments.

The detector 124 is sensitive to radiation (e.g., x-ray) emitted by theradiation source unit 112. In some embodiments, the detector 124 can bea detector array comprising multiple radiation detectors. The detector124 can be disposed opposite the x-ray source unit 112 on rotatinggantry portion 104. In some embodiments, the detector 124 includes amulti-slice detector having a plurality of detector elements extendingin the axial and transverse directions. Each detector element candetects radiation emitted by the radiation source unit 112 thattraverses the examination region 108 and can generate correspondingoutput signals or projection data indicative of the detected radiation.Other detector configurations, such as those wherein stationarydetectors surround the examination region, can also be used.

The motion of the radiation source and emission of radiation thereby arecoordinated to scan a volume of interest (VOI) 122 such as anatomy, or aportion of anatomy, disposed within the examination region 108. Thevolume of interest can be enhanced with a contrast agent in someembodiments, such as described below, for example. In some embodiments,coordinated motion and radiation emission can be used for fly-byscanning, for example. In some embodiments, the radiation source anddetector move in coordination with a contrast agent through the subjectsuch that the VOI is scanned in coordination with the flow of the agentas it is traced through the VOI. In another embodiment, the axialadvancement is coordinated with a motion of the subject to capture adesired motion state.

The support 126 can support a subject, such as a human patient forexample, in which the VOI is defined within the examination region 108.As illustrated in FIG. 1, a drive mechanism 116 can move the radiationsource longitudinally along a z-axis 120 on tracks 128 while the support126 is stationary. In some embodiments, however, the support 126 can betranslated axially along the z-axis 120 while the gantry 104 rotates ina fixed location along the z-axis. An operator of the system can definethe VOI to encompass the whole subject or a portion thereof forscanning. In one embodiment, the CT scanner performs a helical scan ofthe VOI by rotating around the axis 120 during relative movement of thegantry and the support parallel to the axis.

The system 100 can further comprise various computer hardware andsoftware modules. As illustrated in FIG. 1, for example, the system cancomprise data memory 130, a processor 132, a volume image memory 134, auser interface 136, and one or more controllers, such as a CT controller128 and a collimator controller 140. In some embodiments, a singlehardware or software module can control multiple parts of the system110, such as the radiation source and one or more collimators, forexample.

The projection data generated by the detector 124 can be stored to adata memory 130 and reconstructed by a processor 132 to generate avolumetric image representation therefrom. The reconstructed image datacan stored in a volume image memory 134 and displayed to a user via auser interface 136. Although FIG. 1 separately illustrates the datamemory 130 and the volume image memory 134, both can be stored withincommon data storage hardware. The image data can be processed togenerate one or more images of the scanned region or volume of interestor a subset thereof.

The user interface 136 facilitates user interaction with the scanner 102and can comprise various input and output devices.

Software applications and modules can receive inputs from the userinterface 136 to configure and/or control operation of the scanner 102,and other elements of the system 100. For instance, the user caninteract with the user interface 136 to select scan protocols, andinitiate, pause, and terminate scanning. The user interface 136 candisplay images, facilitate manipulation of the data and images andmeasurement of various characteristics of the data and images, etc.

An optional physiological monitor (not shown) can monitor cardiac,respiratory, or other motion of the VOI. For example, the monitor caninclude an electrocardiogram (ECG) or other device that monitors theelectrical activity of the heart. This information can be used totrigger one or more scans or to synchronize scanning with the heartelectrical activity to reduce or eliminate adverse affects of heartmotion on imaging. An optional injector (not shown) or the like can beused to introduce agents, such as contrast for example, into thesubject. Introduction of the agent can be used to trigger one or morescans.

The CT controller 138 can control rotational and axial movement of theradiation source unit 112 and the detector 124 relative to the support126. The CT scanner and CT controller can be coupled to a collimatorcontroller 140 that controls a collimator 142 positioned between theradiation source and the examination region 108. Although FIG. 1illustrates the CT controller and the collimator controller as separateunits, the CT scanner and one or more collimators can be controlled bythe same hardware and software modules in some embodiments.

The collimator controller 140 can control movement, and opening andclosing, of a radiation delivery window of the collimator 142. In someembodiments, the collimator controller can independently controlmovement of individual leaves of the collimator. The collimatorcontroller can be a software module configured to move leaves of acollimator to allow passage of radiation toward a region of interestwhile blocking radiation to portions of a subject outside the region ofinterest.

In some embodiments, the collimator controller 140 can cause thecollimator to function as a shutter to block radiation between scans andto open, close, and translate as the rotatable gantry 104 (andaccordingly the source unit 112 and detector 124 coupled thereto) movearound the VOI 122 during a scan.

In some embodiments, the collimator controller 140 can include one ormore electro-mechanical servo motors. In some embodiments, thecollimator controller 140 can include an electronic controller.

Collimation

Repeated large area circular scans and helical scans can be used toperform perfusion CT. By opening, closing, and/or translating thecollimator 142, radiation can be delivered primarily only along pathsthat intersect the VOI, thereby reducing the X-ray dose. In the case ofhelical scans, a dynamic axial collimator can be used to limit the x-rayexposure, axially, at either end or both ends of the helical scan. Forexample, in some embodiments, an axial collimator can be graduallyopened at the leading end of the VOI and closed at the trailing end ofthe VOI. A dynamic transverse collimator positioned in a planetransverse to a gantry rotation axis and in front of the x-ray sourcecan limit the x-ray exposure to a region of interest (ROI) 144 within afield of view (FOV) 146, as illustrated in FIG. 3. FIG. 3 is a schematicillustration of an imaging system showing two positions 152, 154,respectively at 0 and 90 degrees relative to a subject, of the radiationsource unit 112, detector 124, and a dynamic transverse collimator 142for an off-center ROI 144 surrounding the heart. FIG. 4 illustrates theoutline of a VOI corresponding to the heart. Transverse and axialcollimators can together limit the x-ray exposure to primarily only theVOI 148 for the heart illustrated in FIG. 4, for example. Asillustrated, for example, in FIG. 4, the VOI 148 can include multipleROIs 144.

In some embodiments, a collimator can comprise a first leaf 170 and asecond leaf 172 respectively bounding first and second opposing sides ofa radiation delivery window 174, as illustrated in FIG. 5, for example.The first leaf and the second leaf can be movable to adjust at least oneof a size or a location of the radiation delivery window relative to theradiation source in a direction non-parallel to the axis. The first leafand the second leaf can be independently movable relative to theradiation source in a direction non-parallel to the axis. The first leaf170 and the second leaf 172 can be moveable independently of each other.Each of the first and second sides can be substantially orthogonal toeach of the third and fourth sides opposing sides of the radiationdelivery window 174. In some embodiments, the first leaf and the secondleaf can be independently movable relative to the radiation source in adirection tangential to a circle (i) centered on the axis and (i)defining a plane that is not parallel to the axis. In some embodiments,the leafs can be movable along guide rails 180, as illustrated in FIG.7.

In some embodiments, the collimator can comprise a third leaf 176 andfourth leaf 178 respectively bounding the third and fourth opposingsides of the window. The third leaf, the fourth leaf, and the window canbe arranged generally along a line that is parallel to the axis ofgantry rotation. The window can be interposed between the third andfourth leaves such that radiation is transmitted between the third andfourth leaves in a direction generally perpendicular to the axis ofrotation. The third leaf and the fourth leaf can be independentlymovable relative to the radiation source with a direction of motionbeing generally parallel to the axis. The third leaf 176 and the fourthleaf 178 can be moveable independently of each other. In someembodiments, the third and fourth leaves can be movable independently ofthe first and second leaves.

The transverse and axial collimators can be driven by the same motor ordifferent motors. Similarly, the transverse and axial collimators can becontrolled by the same hardware or software modules. In someembodiments, transverse and axial collimators can be integrated into asingle unit.

The VOI can be defined, for example, by a previously-acquired very lowdose scan of the same region or two orthogonal localizer scans could beused. An operator can specify an axial extent of the VOI and the size,shape, and location of each ROI along the axial direction. In someembodiments, an outline of the entire VOI can be drawn from twoorthogonal views, e.g. sagittal and coronal views, with the imageszoomed according to the largest ROI in the sequence. The truncatedregion of each reconstructed image can be displayed with a darkbackground.

The axial collimator leaves can be opened and closed based on the axialextent of the VOI. If the VOI is modeled using ellipticalcross-sections, the transverse collimator leaves can move smoothly asthey closely follow the outline of the VOI. In the case of a largecone-beam, the beam already encompasses a large portion of the VOI,therefore there can be less narrowing of the VOI profile at the ends ofthe scan.

As in the case of the axial collimator, the position of the dynamictransverse collimator leaves can be based on the couch position.However, in the case of the dynamic transverse collimator, as the couchmoves in the axial direction, the rotation angle can be used todetermine where the current ROI is situated with respect to the source.Given both the couch position and rotation angle, the leaves cancontinuously follow the outline of the overall VOI. For example, in thecase of the cardiac scan shown in FIG. 4, the collimator leaves canfollow the ROIs located along the cardiac volume based on the couchlocation of the ROI as well as the rotation angle of the x-ray source.The ROI along the cardiac volume can have both a non-circular (e.g.,elliptical) shape and a location away from a scan center 150.

In some embodiments, for a sequence of axial or circular scans, one ROIcan be determined for each scan in the sequence. For each scan, therotation angle can be used alone to determine the motion of thecollimator leaves, adjusting for an off-center and/or non-circular ROI.

In some embodiments, the size of the radiation delivery window 174between movable leaves of the transverse collimator can be adjustedprior to a scan and held in a fixed arrangement during the scan. Forexample, a low dose can be performed to identify a VOI, then asubsequent scan can be performed with an transverse collimator aperturedimension selected for imaging of the VOI while the transversecollimator leaves remain stationary during the scan. In someembodiments, the moveable leaves can comprise secondary windows andattenuating members, as discussed further below.

In some embodiments, the collimator can comprise a primary radiationdelivery window 174 of a fixed size. In some embodiments, between scans,a collimator having a window of a first fixed size can be removed fromthe CT scanner 102 and can be replaced with another collimator having awindow of a second fixed size, different than the first fixed size. Thecollimators with primary radiation delivery windows of a fixed size cancomprise secondary windows and attenuating members, discussed furtherbelow, in some embodiments.

As illustrated in FIG. 8, attenuation information from the tissuesurrounding the collimated ROI is desirable due to the extent of theconvolution involved in image reconstruction. Attenuation informationfor the material outside the collimated VOI can be acquired tofacilitate accurate reconstruction. This can be accomplished in variousways, including one or more of the following: (1) use thepreviously-acquired very low dose scan mentioned above to measure theattenuation outside the VOI; (2) use heavily-attenuated rays through theouter portions of the collimator, providing an estimate of theattenuation outside the VOI so long as the collimator attenuation ispreviously calibrated; (3) use a projection-completion estimate,extrapolating the truncated projections using a curve-fit based on asimple model; or (4) use limited, but known, attenuation information forisolated sub-regions in the surrounding tissue.

In some embodiments, attenuation values for the region outside the ROIcan be determined from radiation passing through windows in a gratingthat are separated from a primary window configured to allow passage ofrays of radiation that would travel through the ROI.

FIG. 9 shows an example of a display output, such as can be displayed ona monitor of a scanner, of a CT scan of an anthropomorphic thoraxphantom using a grated collimator. The image of the display output isshown without application of any correction. In some embodiments,correction can be applied to the data used to form the image. In someembodiments, correction can be applied to image data before displayingan image. The VOI in the image of FIG. 9 includes a phantom cardiacregion near the center of the thorax phantom.

In some embodiments, the collimator 142 can comprise a first grating 170and a second grating 172 positioned on opposing sides of a primaryradiation delivery window 174. Each of the first and second gratings cancomprise a plurality of attenuating members 182 with a plurality ofsecondary radiation delivery windows 184 extending between adjacentattenuating members of the first grating and the second grating,respectively.

A width of each secondary window can be less than a width of the primarywindow, as illustrated in FIG. 6, for example. Although FIG. 6illustrates attenuating members of the first grating and the secondgrating as being integral with each other, the first and second gratingscan be part of separate first and second leaves 170, 172, as illustratedin FIG. 7, for example. A total area of each of the secondary windowscan be less than a total area of the primary window. In someembodiments, the width of each secondary window can be proportional to adistance between the secondary window and the primary window, asillustrated in FIG. 7, for example. For example, the width of eachsecondary window can be linearly, exponentially, or geometricallyproportional to the distance between the secondary window and theprimary window. The width of each secondary window can be positivelyproportional to the distance between the secondary window and theprimary window such that the width of the windows increase with theirdistance from the primary window. The secondary windows can be orientedgenerally parallel to sides of the primary window. The secondary windowscan comprise open passages extending through the grating. In someembodiments, the secondary windows can comprise panes of substantiallyradio-transmissive or low-attenuating material. When panes oflow-attenuating material are employed, the panes can attenuate theradiation to a lesser extent than the attenuating members 182.

A width of each attenuating member, and thus the spacing betweensecondary windows, can be proportional to a distance between theattenuating member and the primary window, as illustrated in FIG. 7, forexample. The width of each attenuating member can be linearly,exponentially, or geometrically proportional to the distance between theattenuating member and the primary window. The width of each attenuatingmember can be positively proportional to the distance between theattenuating member and the delivery window. The attenuating members canbe oriented generally parallel to sides of the primary window. In someembodiments, the attenuating members can block passage of x-rayradiation therethrough. In some embodiments, the attenuating members canbe made of materials that substantially prevent transmission of x-rays.The attenuating members can be made of lead, tungsten, or othermaterials or combinations thereof.

In some embodiments, the size, number, position, spacing, or acombination thereof of the secondary windows and attenuating members canprovide approximately a minimum or a near-minimum amount of radiationtransmission for detector operation.

Collimator Control

The collimator controller, which can be a hardware or software module,can be configured to control operation of transverse dynamic collimatorsto significantly reduce the radiation dose delivered by CT scans. Insome embodiments, the collimator controller can control both axial andtransverse collimators. Further details regarding axial collimators andtheir control are provided in U.S. Patent Application Publication No.2010/0246752 to Heuscher et al., entitled Dynamic Collimation in ConeBeam Computed Tomography to Reduce Patient Exposure, the entirety ofwhich is hereby incorporated herein by reference. In some embodiments, asingle collimator can be configured for both axial and transversecollimation. A axial collimator and a transverse collimator can beintegrated as a single unit in some embodiments. The transverse dynamiccollimator, whether alone or in combination with the axial collimator,can be used for both helical and axial scans.

In some embodiments, the leaves of the axial and transverse collimatorscan be moved such that only or substantially only that radiation, e.g.,x-rays, that intersects a predefined VOI is exposed to the patient.

In some embodiments, control of the transverse collimator involves thevelocity of each leaf. The velocity of each leaf can be determined for aregion of interest (ROI) at a given distance from scan center. In someembodiments, the ROI in a particular slice can be circular ornoncircular. The velocity and acceleration of leaf movement depend onhow far off-center a given cross-sectional region of interest (ROI) islocated from a scan center within a field of view (FOV).

Referring to FIG. 10, the following equations can define the transversecollimator leaf position Q(t) and approximated velocity Q′ given therotation speed ρ, collimator distance C, distance S from an idealradiation point source to the scan isocenter, ROI radius R₁, and offsetR₀ at angle θ₀.

$\begin{matrix}{\mspace{79mu}{{Q(t)} = {C \cdot {\tan\left( {{\arcsin\left( \frac{R_{1}}{L(t)} \right)} + {\arcsin\left( {\frac{R_{0}}{L(t)} \cdot {\sin\left( {{\theta(t)} - \theta_{0}} \right)}} \right)}} \right)}}}} & (1) \\{\mspace{79mu}{{L(t)} = \sqrt{\left( {S \cdot {\sin\left( {{\theta(t)} - \theta_{0}} \right)}} \right)^{2} + \left( {{S \cdot {\cos\left( {{\theta(t)} - \theta_{0}} \right)}} - R_{0}} \right)^{2}}}} & (2) \\{{\frac{\partial{Q(t)}}{\partial t} \approx {Q^{\prime}(t)}} = {\frac{C \cdot \pi \cdot R_{0}}{\rho \cdot S} \cdot \frac{\left( {{\cos\left( {{\theta(t)} - \theta_{0}} \right)} - {\frac{R_{1}}{S} \cdot {\sin\left( {{\theta(t)} - \theta_{0}} \right)}} - \frac{R_{0}}{S}} \right)}{\left( {1 - {\frac{R_{0}}{S} \cdot {\cos\left( {{\theta(t)} - \theta_{0}} \right)}}} \right)^{2}}}} & (3)\end{matrix}$

L(t) can represent the distance from the ideal radiation point source tothe center 156 of the ROI and can be used to obtain the angle betweenthe line 158 of length L and the central ray of the projection (line 160of length S). This angle can be added to the remaining angle between theline 158 and the line 162 tangent to the ROI. The distance Q(t) of thecollimator leaf from the central ray can be obtained by multiplying thetangent of the resulting angle by a total distance C between thecollimator 142 and the point source.

The derivative of the expression for Q(t) can be calculated to calculatethe velocity Q′. Assuming a constant rotation speed ρ, the expression2πt/ρ can substituted for θ(t). Due to its complexity, the derivative ofthis equation, δQ(t)/δt, can be calculated numerically. In someembodiments, approximations can be made to obtain a closed formexpression for obtaining the derivative of the equation δQ(t)/δt. Byassuming R₀ and R₁ are relatively small compared to the point source toisocenter distance S, the higher order terms in the Taylor seriesexpansions of both Q(t) and δQ(t)/δt can be eliminated and a goodapproximation Q′(t) can be obtained as shown in equation (3).

The leaves of the axial collimator can be opened at the beginning of ascan, e.g., a helical scan, and closed at the end such that only thatradiation, e.g., x-rays, that intersect the VOI are exposed to thesubject, as illustrated in FIGS. 11 and 12 for the right end of thescanned volume, for example. As the beam, e.g., a cone-beam, approachesthe cylindrical VOI from the right, the leaves can be closed, shifted tothe far left. As the left edge of the beam touches the far edge of thecylinder, the right leaf can begin opening by moving to the right untilthe center of the beam reaches the edge of the cylinder. The right leafthen can immediately accelerate to a higher velocity to be able tofollow the near edge of the cylinder, until the entire beam is exposed.The collimator can remain open as the scan proceeds until the left edgeof the beam hits the near edge of the left side of the cylinder, atwhich point the left collimator leaf can begin closing in reverse orderfrom the previous sequence for the right leaf.

The following equations can define the axial collimator position Q(t)and velocity δQ/δt given the helical pitch P, helical position H(t),rotation speed ρ, detector width w, collimator distance C, point sourceto isocenter distance S, and cylindrical VOI radius R:

$\begin{matrix}{{{H(t)} > {0\text{:}\mspace{14mu}{Q(t)}}} = {{{\frac{C \cdot w}{2 \cdot S} \cdot \left( {1 + \frac{2 \cdot P \cdot t}{\rho \cdot \left( {1 + \frac{R}{S}} \right)}} \right)}\frac{\partial{Q(t)}}{\partial t}} = \frac{C \cdot w \cdot P}{\rho \cdot \left( {S + R} \right)}}} & (4) \\{{{H(t)} < {0\text{:}\mspace{14mu}{Q(t)}}} = {{{\frac{C \cdot w}{2 \cdot S} \cdot \left( {1 + \frac{2 \cdot P \cdot t}{\rho \cdot \left( {1 - \frac{R}{S}} \right)}} \right)}\frac{\partial{Q(t)}}{\partial t}} = \frac{C \cdot w \cdot P}{\rho \cdot \left( {S - R} \right)}}} & (5)\end{matrix}$

From right to left, as the beam, e.g., cone-beam, approaches thecylindrical VOI, the collimator can attenuate all rays outside the faredge of the cylinder (H(t)>0). Once the center of the beam passes theend of the cylinder (H(t)<0), the collimator can attenuate all raysinside the near edge of the cylinder. Consequently, the denominator ofthe equations correspondingly changes from (S+R) to (S−R) betweenequations (4) and (5).

FIGS. 13 and 14 are plots of the velocities (in cm/s) for a transversecollimator leaf where θ₀=0, S=70, and ρ=0.3 s/rev. In FIG. 13, C=27,R₀=18, and R₁=6. In FIG. 14, C=12, R₀=6, R₁=6. As illustrated in FIG.13, for a ROI of 12 cm within a 48 cm diameter FOV and an offset R₀ of18 cm, the transverse collimator leaf can achieve a maximum velocity of198 cm/s. On the other hand, as illustrated in FIG. 14, if thecollimator is located 12 cm from the idealized radiation point sourceand if the subject is positioned such that the ROI is 12 cm closer tothe scan center, the collimator leaf reaches a maximum velocity of 24cm/s for an offset of 6 cm. Therefore, some embodiments include movingthe transverse dynamic collimator closer to the radiation point source,moving the subject closer to the scan center, or both.

FIG. 15 is a plot of the velocities (in cm/s) for a transversecollimator leaf where θ₀=0, S=70, ρ=0.3 s/rev, C=12, R₀=18, and R₁=6.Thus, if a velocity of 100 cm/s or less can be tolerated and thecollimator is located within 12 cm of the idealized radiation pointsource, an off-center ROI can be tracked by the collimator and, thus, asubject can remain in the same position within the FOV between apreliminary full-field scan and subsequent scanning targeting to theVOI. FIG. 6 shows that a maximum velocity of 87 cm/s is reached for a 12cm ROI located 18 cm off-center according to the equations providedherein.

FIGS. 13-15 also compare the closed form approximation Q′ (dashed line)with the actual velocity δQ/δt (solid line) computed numerically fromQ(t). The close match between the two curves confirms the validity ofthe approximation for the range of geometric values simulated.

FIG. 16 is a plot of the velocities (in cm/s) for leaves of an axialcollimator where C=27 cm, S=70 cm, a detector width w is 8 cm, a pitchfactor P is 1.4, rotation speed ρ is 0.3 sec/rev, and a VOI has a radiusR of 25 cm. FIG. 16 shows a maximum axial collimator leaf velocity of22.9 cm/s. That maximum velocity occurs for H(t)<0, when the center ofthe cone-beam passes the edge of the cylinder closest to the x-raysource.

The velocity profiles of the transverse collimator leaves and the axialcollimator leaves can be compared. The maximum velocity incurred by theaxial collimator leaves during a typical helical scan with an 8 cmdetector, 0.3 second rotation time (i.e., revolution duration), with apitch factor of 1.4 is 22.9 cm/sec. On the other hand, the maximumvelocity of a transverse collimator positioned 27 cm from the source is198 cm/sec for a 12 cm cardiac scan located 18 cm from the scan center.Thus, the velocities of the transverse collimator can be greater thanthe helical collimator. For a transverse collimator mounted 27 cm fromthe x-ray source, e.g., just beyond the opening of the gantry, themaximum velocity incurred can be more than 8 times that of the axialcollimator. However, if the collimator is located closer to the sourceand if the VOI is positioned, or possibly repositioned, 12 cm or lessoff-center, the velocities of the transverse and axial collimators canbe comparable. In some embodiments, a motor and control system for atleast the transverse collimator can provide leaf velocities up to 90cm/s, patient repositioning can be avoided in more instances. In someembodiments, a motor and control system for at least the transversecollimator can provide leaf velocities greater than 90 cm/s.

Although movement of leaves in a transverse dynamic collimator have beendiscussed in connection with placement at 12 cm and 27 cm from theradiation source, a transverse dynamic collimator can be positioned atother distances from the radiation source. For example, the transversedynamic collimator can be positioned within about 27 cm, about 20 cm,about 15 cm, or about 10 cm of the radiation source in some embodiments.In some embodiments, the collimator can be integrated into the radiationsource unit 112. By integrating a transverse dynamic collimator into theradiation source unit 112, the distance from the radiation source(measured from the idealized point source location) can be shorter and,thereby, reduce the dynamic requirements (velocity and acceleration) ofthe transversely moving leaves. However, the distance between theidealized point source and the transverse dynamic collimator ispreferably sufficiently long that the size of the radiation penumbra isacceptable. For example, in embodiments that comprise a gratedcollimator, the distance between the idealized point source and thetransverse dynamic collimator is preferably sufficiently long to avoidcrosstalk between adjacent secondary windows, e.g., slots, in the gratedcollimator.

Dynamic Transverse Collimation Dose Reduction

Modeling of heart and kidney scans, with and without transverse dynamiccollimation, indicate significant skin dose reduction in both cases.Elliptical models were analyzed to determine the skin exposure for heartand kidney scans. A dose of radiation, e.g., X-rays, exposed to thesubject, e.g., a patient, can be significantly reduced using a dynamictransverse collimator such as that illustrated in FIG. 5, for example.The use of other dynamic transverse collimators, such as the grateddynamic transverse collimator illustrated in FIG. 7, can alsosignificantly reduce radiation dose.

FIG. 17 shows three cross-sections from the middle of a fivecross-section sequence. A target ROI corresponding to a heart isrepresented by an ellipse in each cross-section of FIG. 17. Dynamictransverse collimation can follows the ellipses outlining the heart andrepresenting the target ROI. The cross-sections of FIG. 17 also includebody outlines, approximated with ellipses, from which the skin exposurevalues were calculated. The live sections of the heart were equallyspaced. In the un-collimated case, all sections are fully exposed, whilein the collimated case, the exposure is limited to the target VOI, withthe first and last sections fully collimated down to a 0 cm diametercircle. Reference lines are shown in FIG. 17 that intersect the scancenter, the body ellipse, and target ROI.

The average un-collimated skin exposure relative to the average exposureat the center of the target ROIs is compared to the average collimatedskin exposure over the five slices again relative to the averageexposure at the center of the target ROI. For the exposure analysis ofthe heart, reconstructions of an XCAT phantom were used with an X-raysource radius S of 57 cm. A compensator in front of the X-ray source canprovide a more uniform signal to the detector and can reduce the overalldose to the patient. Therefore a compensator was modeled thatcompensates for a disc with a radius rc of 24 cm and an attenuationcoefficient equal to water (0.183/cm at 80 KeV, approximately theaverage energy for a typical CT system performing 120 KeV scans).

As an initial approximation, the water attenuation value of 0.183/cm wasassumed for all path lengths throughout the body. The exposure for eachof 100 points equally spaced in angle β on the surface of the bodyellipse was calculated for 1000 angular views, θ, of the source covering360 degrees. Rays emanating from the source pass either just through thecompensator (FIG. 4), or both through the compensator and the body (FIG.5). These exposure values were averaged over the 1000 views. Theexposure at the center of the target ROI (FIG. 6), was averaged over1000 views. This provided a reference for the skin exposure values.Thus, all overall skin exposure values were measured as a ratio withrespect to the exposure at the center of the target ROI.

For the scans utilizing a dynamic collimator, the fan angles for whichthe collimated x-rays intersect tangentially to the target ROI werecalculated for each x-ray source position and used to exclude allexposure from the x-ray source that fell outside the correspondingangular range. Again, all skin exposure values were averaged over 1000views.

In the case of the heart, 5 equally-spaced sections of the heart wereused to define the cardiac VOI, with the first and last sections fullycollimated. The relative skin dose for the center section was comparedwith and without dynamic collimation. The final skin exposure valueswere averaged over the five sections, both with and without dynamiccollimation.

The boundaries of the ellipses were defined by specifying 6 user-definedpoints around the periphery of both the body outline and target ROI. Aleast-squares solution to the parameters of each ellipse, (a, b, r0, t0,tr)=(major axis, minor axis, polar radius of the origin of the ellipse,polar angle of the origin, and angular orientation of the ellipse), wasthen obtained given the (R,T) polar coordinates of these 6 points alongwith the following constraints:

${\frac{X^{2}}{a} + \frac{Y^{2}}{b}} = {{1\mspace{14mu}{and}\mspace{14mu}{{{tr} - \frac{\pi}{2}}}} < \frac{\pi}{2}}$where:X=R·cos(T−tr)−r0·cos(t0−tr)Y=R·sin(T−tr)−r0·sin(t0−tr)(R,T) correspond to the polar coordinates of the 6 points and thefollowing initial values are provided:(a, b, r0, t0, tr)=(TOL, TOL, com(R,T), mean(T), TOL)where:com(R,T)=√{square root over (mean(R·cos(T))²+mean(R·sin(T))²)}{squareroot over (mean(R·cos(T))²+mean(R·sin(T))²)}TOL=tolerance value=0.00001.

Given both the body and target ellipses along with the compensatorattenuation as a function of the fan angle, the skin exposures wascalculated. For all ray angles up to the tangent to the body ellipse,the exposure was the attenuated exposure through the compensator (FIG.18). For all other angles for which the rays pass through the body tothe selected point on the ellipse, the x-ray exposure is furtherattenuated by the path length through the body. Given the source radius,source angle, and point on the body ellipse, the path length p relativeto the distance p0 (FIG. 19) can be calculated as a solution to aquadratic equation resulting from the condition that the entrance pointof the ray also satisfies the equation for the body ellipse.

A point on the skin was treated like any other point within the bodyellipse. In the case of a point on the boundary of the ellipse directlyexposed by the x-ray source, the path lengths through the body convergeto zero at all angles up to those angles tangent to ellipse.

FIG. 18 illustrates geometry for a ray at angle α directly exposing theskin, emanating from the x-ray source located at angle θ. The rayillustrated in FIG. 18 is only attenuated by the compensator as afunction of angle α.

FIG. 19 illustrates another geometry for a ray at angle α indirectlyexposing the skin, emanating from the x-ray source located at angle θ.The ray illustrated in FIG. 19 is further attenuated by the body pathlength (1−p)□p0.

The resulting skin exposure is then calculated as an average value over360 degrees of the angular position (θ) of the x-ray source:

${{Exposure}(\beta)} = {{.001} \cdot {\sum\limits_{i = 1}^{1000}{\left( {{intensity}\left( {\alpha\left( {\beta,\theta_{i}} \right)} \right)} \right) \cdot {{att}\left( {\beta,\theta_{i}} \right)}}}}$where:β=the angle of the point on the body ellipseθ=the source angleα=fan angle of the ray intersecting the point on the body ellipse

${{intensity}(\alpha)} = e^{2.183 \cdot {({\sqrt{{r\; c^{2}} - {({{S \cdot \sin}\;\alpha})}^{2}} - {r\; c}})}}$att(β,θ)=e ^(−0.183·(1−p(β,θ))·p0(β,θ))

p is the path length to the entrance point on the body ellipse relativeto p0; and

p0 is the path length to the selected point on the body ellipse.

The average relative skin exposure is then the average of the exposurefor all points around the body ellipse divided by the exposure at thecenter of the target ROI. For the average collimated exposure, the sameexposure equation is used, but with the intensity set to zero for allray angles whose fan angle exceeds that of the range of angles spannedby the two rays that intersect the tangents to the target ellipse, i.e.:intensity(α(β,θ))=0 if α>AC(θ) or α<ACC(θ)AC is the clockwise angular position of the collimator leaf for sourceangle θ; andACC is the counter-clockwise angular position of the collimator leaf.

Finally, the exposure at the center of the target ROI is calculated as areference for the skin exposure values. In this case, p0 corresponds tothe path length to the point at the center of the target ellipse and pis calculated as the relative path length to the point on the bodyellipse (FIG. 20). As this is the center of the target ellipse, the samevalue applies whether or not dynamic collimation is used. FIG. 20illustrates geometry for a ray at angle α exposing the center of thetarget ROI. The ray of FIG. 20 is further attenuated by the body pathlength (1−p)□p0.

For the kidneys, ellipses were used to outline the target ROI and bodyof the patient. A single multi-slice scan was used to acquire the kidneyperfusion images with the central image shown in FIG. 21. The averagerelative (un-collimated) skin dose was compared to the average relative(collimated) skin dose.

A second kidney study was used to not only corroborate the results ofthe first study, but to demonstrate the additional dose savings thatwould be achieved for a whole-organ kidney study. Five equally-spacedsections (FIGS. 22A-E) were selected spanning the entire kidney with thefirst and last sections fully collimated when utilizing dynamiccollimation. The central section was used to compare with the centralsection of the previous study and the overall whole-organ un-collimated(relative) kidney dose was compared with the overall dynamicallycollimated (relative) kidney dose.

The reduction in skin exposure that can be achieved using transversedynamic collimation of heart and kidney scans was calculated using theabove-described elliptical models. The results, collimated andun-collimated exposure values relative to the average exposurecalculated at the center of the target ROI, are summarized in Table 1below:

TABLE 1 Un-collimated Collimated Exposure Exposure Exposure ReductionHeart 2.61 1.2 2.1:1 Whole Organ 2.605 .704 3.7:1 Kidney Study I 2.5451.58 1.61:1  Kidney Study 2.1 1.0 2.1:1 II Whole Organ II 2.1 .584 3.6:1

These results indicate a significant skin dose reduction for both heartand kidney scans. A 3.7:1 reduction in skin exposure was calculated forthe whole-heart scan. A 1.6:1 to 2.1:1 reduction in skin exposure wascalculated for a kidney scan and a 3.6:1 reduction for a whole organkidney scan (both kidneys are included in the target ROI).

The reduced skin exposure calculated for heart and kidney scansdemonstrates the significant benefit of transverse dynamic collimation,especially to whole organ studies. Skin exposure values are 2.1 to 2.6times higher than the exposure at the center of the target ROI, evenwith an x-ray compensator. This demonstrates how important it is to keepskin exposure values as low as possible.

Dynamic collimation to target the VOI can greatly reduce patient dose(up to 4:1 reduction in skin exposure for whole organ cardiac and kidneyscans). This reduction in dose may enable coronary CT angiography to beused on a much more routine basis. Likewise, significantly reducing thedose for CT perfusion scans and whole organ kidney scans will greatlybenefit the clinical use of such scans. Dynamic collimation can greatlyreduce dose for other clinical applications as well.

Sampling Frequency Control

In some embodiments, radiation dose delivered to a patient can bereduced by varying a scanning frequency or interval between scans duringa series of scans. FIG. 23 illustrates a method of contrast-enhancedcomputed tomography (CT) imaging. The following description of FIG. 23refers to FIG. 24, which schematically illustrates a curve 2410representing a magnitude of radiation attenuation (vertical axis) by acontrast-enhanced structure over time (horizontal axis), and a threshold2412. In some embodiments, the threshold 2412 is 35 HU. In someembodiments, the threshold can be other predetermined attentiondensities, such as 50, 75, or 100 HU, for example. In some embodiments,the threshold comprises a degree of increase, e.g., a percentage, in theattenuation compared to a value indicated by an initial scan.

At step 2310, scanning can begin at a first rate while monitoring for anincrease of attenuation above the threshold 2412. At step 2312, afterdetection of the increase of attenuation above the threshold, the rateof change of attenuation can be determined between scans. At step 2314,when the rate of change of attenuation decreases (corresponding to aninflection point 2414 on the ascending part of the curve 2410), the rateof scanning can be increased. At step 2316, when the rate of change ofattenuation becomes negative (corresponding to a peak 2416 of the curve2410), the rate of scanning can be decreased. In some embodiments, thefrequency is reduced at step 2316, in response to detection of adecrease in attenuation. For example, the scan interval can be lengthenfor a next scan upon detecting a first decrease in attenuation after theincrease above the threshold 2412.

At step 2318, when the rate of change of attenuation decreases(corresponding to an inflection point 2418 on the descending part of thecurve 2410), the rate of scanning can be further decreased. The rate canbe further decreased in some embodiments by increasing a scan intervalwith each successive scan. In some embodiments, the scan interval can beapproximately doubled with each successive scan.

Scanning can be terminated at step 2320 in response to expiration of apredetermined period of time, completion of a predetermined number ofscans, increase of a scan interval beyond a predetermined interval, orother trigger. In some embodiments, if a remaining time between a latestscan and an end of the predetermined period is less than an intervalbetween the latest scan and an immediately preceding scan, a penultimatescan can be performed at approximately half of the remaining time afterthe latest scan and a final scan can be performed at the end of thepredetermined period.

FIG. 25 is an exemplifying plot of magnitudes of radiation attenuationby various contrast-enhanced structures over time. The vertical axiscorresponds to attenuation density in Hounsfield Units. The horizontalaxis corresponds to time in seconds. In FIG. 25, the large circlesrepresent scans initiated by a sampling frequency adjustment accordingto an embodiment. Small circles correspond to scans obtained at each of70 seconds. Squares in FIG. 25 represent attention through the LADterritory as detected by scans each second. FIG. 25 shows thatapplication of a sampling frequency or interval adjustment can result in18 scans compared to 70 scans if a scan is performed each second.Triangles in FIG. 25 represent attention through remote territory asdetected by scans each second.

The methods described herein for controlling contrast-enhanced computedtomography imaging can be implemented by computer system. For example,such a system can comprise an attenuation monitoring and ascanning-frequency control module. The monitoring module can beconfigured to begin monitoring of the rate of change after detection ofcompliance of the attenuation with the threshold 2412. In someembodiments, the system can further comprise a processing moduleconfigured to generate a representation of a relationship between timeand radiation attenuation by a second structure within the targetregion. In some embodiments, the system can further comprise atermination module configured to terminate the scanning

The attenuation monitoring module can be configured to monitor, duringan imaging session, an indicator of attenuation of radiation by acontrast-enhanced structure within a target region. The monitoringmodule can be configured to monitor a rate of change of the attenuation.

The scanning-frequency control module configured to (i) increase afrequency of scanning from a first rate to a second rate after detectionof an increase of the attenuation, and (ii) decrease the frequency to athird rate after detecting a decrease in attenuation after increasingthe frequency to the second rate. The scanning-frequency control modulecan be configured to increase the frequency to the second rate inresponse to detection of a decrease in a rate at which the attenuationis increasing. The scanning-frequency control module can be configuredto decrease the frequency below the third rate in response to detectionof a decrease in a rate at which the attenuation is decreasing. Thescanning-frequency control module can be further configured to decreasethe frequency further below the third rate with each successive scan.The scanning-frequency control module can be configured to divide thefrequency by approximately two with each successive scan. Thescanning-frequency control module can be configured to reduce thefrequency to the third rate upon a first detection of a decrease inattenuation after an increase to the second rate.

The termination module can be configured after a predetermined period oftime and direct performance of a final scan at the end of thepredetermined period. The termination module can be configured toterminate the scanning after a predetermined period of time, and, if aremaining time between a latest scan and an end of the predeterminedperiod is less than an interval between the latest scan and animmediately preceding scan, direct performance of (i) a penultimate scanat a half of the remaining time after the latest scan and (ii) a finalscan at the end of the predetermined period.

Radiation Exposure Control

In some embodiments, radiation dose delivered to a patient can bereduced by varying an applied power during a series of scans. FIG. 26illustrates a method of contrast-enhanced computed tomography (CT)imaging. At step 2610, scanning can be at a first applied power whilemonitoring for an increase of attenuation above the threshold 2412. Atstep 2612, the applied power for each of a plurality of scans can beselected. The applied power can be varied among scans of a series duringa session.

The applied power can be determined, at least in part, by selection ofan applied current. In some embodiments, the applied power can be variedby changing an applied voltage or a resistance. In some embodiments, thepower for a first scan can be a maximum power applied during thesession. In some embodiments, a current applied to a first scan can beabout 200 ma. The applied power can be selected in some embodiments bymultiplying a maximum current by an exponential function based on theattenuation determined from the preceding scan. In some embodiments, theexponential function can yield a value that is (i) greater than aminimum allowable current divided by a maximum allowable current, and(ii) less than 1. In some embodiments, the exponential function can befunction F determined byF=e ^(C·) ^((TH−ΔHU)) ^(/) THwherein TH is a threshold attenuation magnitude and ΔHU is equal to adifference in magnitude, in Hounsfield Units, between the attenuationdetermined from a preceding scan and a baseline attenuation. Thebaseline attenuation can be a magnitude of the attenuation indicatedbased on the initial scan.

In some embodiments, C is selected such that, when the function isapplied, an applied current for a next scan is about a tenth of themaximum allowable current when the attenuation of the preceding scan isabout ten times above the threshold attenuation magnitude. In someembodiments, C can be about 0.25.

FIG. 27 is an exemplifying plot, similar to FIG. 25, of magnitudes ofradiation attenuation by various contrast-enhanced structures over time,and indicates a current magnitude for a plurality of scans. The verticalaxis corresponds to attenuation density in Hounsfield Units. Thehorizontal axis corresponds to time in seconds. In FIG. 27, each largecircle represents a scan and an applied current is identified for eachlarge circle. As shown by FIG. 27, an applied power corresponding to aminimum allowable current can be selected for each scan for which adetermining function, such as the function F for example, indicates,based on the attenuation indicated by a preceding scan, a current lessthan the minimum allowable current.

The methods described herein for controlling contrast-enhanced computedtomography imaging can be implemented by computer system. For example,such a system can comprise an attenuation monitoring and a power controlmodule. In some embodiments, the system can comprise a power controlmodule in addition or alternative to a scanning-frequency controlmodule. The power control module can be configured to select an appliedpower for each of a plurality of scans based on the attenuation detectedfrom a preceding scan. The power control module can be configured todirect application of a maximum power applied during the session in afirst scan. The power control module can be configured to applysubstantially the same amount of power to individual scans untildetection of an increase of the attenuation to or beyond a thresholdattenuation magnitude. The power control module can be configured toselect the applied power by multiplying a maximum current by anexponential function, such as described above.

Additional Methods

The statistics for perfusion curves can be improved with a number ofslices used for a VOI. Thus, in some embodiments, a VOI can utilize morethan one slice. Motion may occur between the reference scan andperfusion series. Registration can be performed for the tissuescontaining the VOIs. Motion correction can be performed between allimages acquired in the series. In some embodiments, motion correctioncan significantly improve the quality and accuracy of the perfusioncurves. For example, motion can occur because of breathing as indicatedby the oscillations repeating approximately every three seconds in theLAD territory data of FIGS. 25 and 27. In some embodiments, motioncontrol can permit further dose reduction while retaining statisticalaccuracy of the perfusion curves and achieving comparable diagnosticresults.

Example of Dosage Reduction Using Scan Frequency Control

A kidney perfusion study was performed applying an embodiment of scanfrequency control.

Kidney perfusion data was acquired using a first protocol. In the firstprotocol, a low dose reference scan was performed. From the referencescan, an axial location and extent of the scan was identified for aperfusion series. The target ROIs were identified. A 60-second scanseries was performed, with each scan being acquired with a tube currentof 200 ma. One scan was performed each second for 60 seconds. Each scanwas directed to a 8 cm circular ROI. FIG. 21 illustrates a sliceobtained from a first person using the first protocol. From the sliceshown in FIG. 21, various perfusion parameters were determined,including mean arterial transit time (MTTa), renal plasma flow (RPF),and glomerular filtration rate (GFR). These parameters are shown inTable 2A, below, as “fully-sampled data.”

Sub-sampled data was obtained by applying a second (emulated) protocolto select a subset of data from the fully-sampled data. According to thesecond protocol, a low dose reference scan would be performed. From thereference scan, the axial location and extent of the scan would beidentified as well as the arterial VOI used to define the motion of atransverse dynamic collimator. The target ROIs would be identified. Thesub-sampled data was selected as though a 60-second scan series had beenperformed with the scanning frequency being adjusted during the seriesas data indicative of the arterial input function (AIF) was acquired.

A sampling algorithm was applied in the second (emulated) protocol. Thesampling algorithm adaptively varied the sampling along the arterialinput function (AIF) which corresponds, to blood flow in the aorta.FIGS. 28 and 29 illustrate the adaptive sampling based on the AIF. Thesecond protocol was applied to select the sub-sampled data from thefully-sampled data as though following steps had been preformed incapturing the data. A first scan took place at time t=0. Another scanwas performed every two seconds after the first scan until the arterialcurve rose above a predefined threshold TH, e.g. 35 HU. After the curverose above the threshold, the slope of the curve was tracked using afinite difference. When the magnitude of the slope was found to havedecreased, the interval between scans was reduced such that one scan wasperformed every second. When the peak of the arterial curve was detectedby the value of the slope becoming negative, the scanning frequency wasmade one scan every 2 seconds. After the inflection point of descent ofthe curve was detected by the magnitude of the slope again decreasing,the scan interval was doubled after each subsequent scan. Very sparsesampling can be performed over the slowly descending exponential portionof the curve. At the end of a predetermined scan period, one final scanwas performed to complete the sampling of the arterial curve.

FIG. 29 illustrates the ROI 144 for the second (emulated) protocol. FIG.28 includes curves 190, 192, 194 corresponding respectively toattenuation by cortex 186, aorta 188, and kidney tissue, shown in FIG.29. FIG. 28 indicates 16 subsamples chosen out of 60. Each subsample isrepresented by a vertical line intersecting an “x.” FIG. 29 correspondsto a subsample 29-29 in FIG. 28. Current magnitudes are indicated inFIG. 28 for each subsample. The minimum current was 40 ma, occurring atthe peak 2816 of the AIF curve, and the maximum current was 200 ma, usedat the beginning of the scan.

From the data obtained using the second (emulated) protocol, variousperfusion parameters were determined, including mean arterial transittime (MTTa), renal plasma flow (RPF), and glomerular filtration rate(GFR). These parameters are shown in Table 2A, below, as “sub-sampleddata.” The structures within the ROIs that were used to generate thecurves used to calculate these parameters included the cortex of thekidney and aorta. The parameters derived from the original fully-sampleddata are compared to those derived from the sparsely-sampled (frequencyadjusted) data in Table 2A.

The kidney perfusion study compared MTTa/RPF/GFR values between originalfully-sampled values and values obtained using sub-sampled data. Table2A summarizes the results of the comparison. Maximum deviation inMTTa|RPF|GFR values is 5%.

TABLE 2A MTTa/RPF/GFR Fully-sampled 8.5|144|34 data Sub-sampled data8.3|141|36

The slice obtained from the first person shown in FIG. 21 (Case I) and aslice obtained from a second person shown in FIG. 22C (Case II) wereused to estimate the dosage reduction that would be obtained though useof sparse sampling, modulated tube current, and dynamic collimation tothe ROI (an elliptical region surrounding both kidneys and aorta). Thoseestimates were compared to the radiation exposure without sparsesampling, modulated tube current, and dynamic collimation to the ROI.The overall exposure reductions were also calculated and compared.

The dosage reduction from sub-sampling was determined based onapplication of the second (emulated) protocol, described above. Thedosage reduction from dynamic collimation was calculated using thecalculation techniques described above under the heading “DynamicTransverse Collimation Dose Reduction.”

The average exposure due to modulated tube current was used to determinethe dosage reduction from modulation of tube current. For both Case Iand Case II, a scan-exposure algorithm was applied to calculate theexposure reduction that would have been attributable to currentmodulation had the algorithm been applied during data acquisition. Thescan-exposure algorithm would have adaptively varied the input currentand, therefore, the emitted radiation during scanning. FIGS. 25 and 27illustrate adaptive scan-exposure control based on the AIF. Given amaximum and a minimum current (ma) allowed, exposure was calculated asthough the following scan-exposure algorithm and procedure had been usedto acquire the data. Scans were performed at the maximum current, e.g.200 ma, until the arterial curve was detected to have risen above thethreshold. Thereafter, the applied current was reduced, using thepredetermined contrast detection threshold TH, by multiplying themaximum current by the following factor F:F=e ^(C·) ^((TH−ΔHU)) ^(/) THwhere:C=0.25(minimum allowable ma)/(maximum ma)<F<1ΔHU=the difference of the Hounsfield Unit value of the curve and thebaseline value corresponding to the first HU value of the curve.

C was chosen such that if the arterial curve rose 10 times above thethreshold TH (e.g., 35 HU), the current would be reduced by 0.1. Forexample, if the attenuation is 275 HU and the baseline is 100 HU(ΔHU=175), then the current would be decreased from a maximum of 200 mato 40 ma. The applied x-ray current was determined for the remainingscans using this formula above for the rest of the series.

Table 2B summarizes the exposure reductions calculated from evaluationof Case I and Case II. The average overall reduction for Case I and CaseII is 10.5:1.

TABLE 2B Case I Case II Sub-sampling Exposure Reduction 3.8:1 3.8:1Current Modulation Exposure 1.5:1 1.5:1 Reduction Dynamic CollimationReduction 1.6:1 2.1:1 Overall Reduction 9.1:1  12:1

Based on the results of this comparison, the second protocol can providediagnostic results comparable to the first protocol. For kidneyperfusion scans, the radiation dose using the second protocol can beexpected to be one-tenth of the radiation dose to the patient using thefirst protocol.

FIG. 30 is a conceptual block diagram illustrating an example of asystem, in accordance with various aspects of the subject technology. Asystem 3001 may be, for example, a client device or a server. The system3001 may include a processing system 3002. The processing system 3002 iscapable of communication with a receiver 3006 and a transmitter 3009through a bus 3004 or other structures or devices. It should beunderstood that communication means other than busses can be utilizedwith the disclosed configurations. The processing system 3002 cangenerate audio, video, multimedia, and/or other types of data to beprovided to the transmitter 3009 for communication. In addition, audio,video, multimedia, and/or other types of data can be received at thereceiver 3006, and processed by the processing system 3002.

The processing system 3002 may include a processor for executinginstructions and may further include a machine-readable medium 3019,such as a volatile or non-volatile memory, for storing data and/orinstructions for software programs. The instructions, which may bestored in a machine-readable medium 3010 and/or 3019, may be executed bythe processing system 3002 to control and manage access to the variousnetworks, as well as provide other communication and processingfunctions. The instructions may also include instructions executed bythe processing system 3002 for various user interface devices, such as adisplay 3012 and a keypad 3014. The processing system 3002 may includean input port 3022 and an output port 3024. Each of the input port 3022and the output port 3024 may include one or more ports. The input port3022 and the output port 3024 may be the same port (e.g., abi-directional port) or may be different ports.

The processing system 3002 may be implemented using software, hardware,or a combination of both. By way of example, the processing system 3002may be implemented with one or more processors. A processor may be ageneral-purpose microprocessor, a microcontroller, a Digital SignalProcessor (DSP), an Application Specific Integrated Circuit (ASIC), aField Programmable Gate Array (FPGA), a Programmable Logic Device (PLD),a controller, a state machine, gated logic, discrete hardwarecomponents, or any other suitable device that can perform calculationsor other manipulations of information.

A machine-readable medium can be one or more machine-readable media.Software shall be construed broadly to mean instructions, data, or anycombination thereof, whether referred to as software, firmware,middleware, microcode, hardware description language, or otherwise.Instructions may include code (e.g., in source code format, binary codeformat, executable code format, or any other suitable format of code).

Machine-readable media (e.g., 3019) may include storage integrated intoa processing system, such as might be the case with an ASIC.Machine-readable media (e.g., 3010) may also include storage external toa processing system, such as a Random Access Memory (RAM), a flashmemory, a Read Only Memory (ROM), a Programmable Read-Only Memory(PROM), an Erasable PROM (EPROM), registers, a hard disk, a removabledisk, a CD-ROM, a DVD, or any other suitable storage device. Thoseskilled in the art will recognize how best to implement the describedfunctionality for the processing system 3002. According to one aspect ofthe disclosure, a machine-readable medium is a computer-readable mediumencoded or stored with instructions and is a computing element, whichdefines structural and functional interrelationships between theinstructions and the rest of the system, which permit the instructions'functionality to be realized. In one aspect, a machine-readable mediumis a non-transitory machine-readable medium, a machine-readable storagemedium, or a non-transitory machine-readable storage medium. In oneaspect, a computer-readable medium is a non-transitory computer-readablemedium, a computer-readable storage medium, or a non-transitorycomputer-readable storage medium. Instructions may be executable, forexample, by a client device or server or by a processing system of aclient device or server. Instructions can be, for example, a computerprogram including code.

An interface 3016 may be any type of interface and may reside betweenany of the components shown in FIG. 30. An interface 3016 may also be,for example, an interface to the outside world (e.g., an Internetnetwork interface). A transceiver block 3007 may represent one or moretransceivers, and each transceiver may include a receiver 3006 and atransmitter 3009. A functionality implemented in a processing system3002 may be implemented in a portion of a receiver 3006, a portion of atransmitter 3009, a portion of a machine-readable medium 3010, a portionof a display 3012, a portion of a keypad 3014, or a portion of aninterface 3016, and vice versa.

FIG. 31 illustrates a simplified diagram of a system 3100, in accordancewith various embodiments of the subject technology. The system 3100 mayinclude one ore more remote client devices 3102 (e.g., client devices3102 a, 3102 b, 3102 c, and 3102 d) in communication with a servercomputing device 3106 (server) via a network 3104. In some embodiments,the server 3106 is configured to run applications that may be accessedand controlled at the client devices 3102. For example, a user at aclient device 3102 may use a web browser to access and control anapplication running on the server 3106 over the network 3104. In someembodiments, the server 3106 is configured to allow remote sessions(e.g., remote desktop sessions) wherein users can access applicationsand files on the server 3106 by logging onto the server 3106 from aclient device 3102. Such a connection may be established using any ofseveral well-known techniques such as the Remote Desktop Protocol (RDP)on a Windows-based server.

By way of illustration and not limitation, in one aspect of thedisclosure, stated from a perspective of a server side (treating aserver as a local device and treating a client device as a remotedevice), a server application is executed (or runs) at a server 3106.While a remote client device 3102 may receive and display a view of theserver application on a display local to the remote client device 3102,the remote client device 3102 does not execute (or run) the serverapplication at the remote client device 3102. Stated in another way froma perspective of the client side (treating a server as remote device andtreating a client device as a local device), a remote application isexecuted (or runs) at a remote server 3106.

By way of illustration and not limitation, a client device 3102 canrepresent a computer, a mobile phone, a laptop computer, a thin clientdevice, a personal digital assistant (PDA), a portable computing device,or a suitable device with a processor. In one example, a client device3102 is a smartphone (e.g., iPhone, Android phone, Blackberry, etc.). Incertain configurations, a client device 3102 can represent an audioplayer, a game console, a camera, a camcorder, an audio device, a videodevice, a multimedia device, or a device capable of supporting aconnection to a remote server. In one example, a client device 3102 canbe mobile. In another example, a client device 3102 can be stationary.According to one aspect of the disclosure, a client device 3102 may be adevice having at least a processor and memory, where the total amount ofmemory of the client device 3102 could be less than the total amount ofmemory in a server 3106. In one example, a client device 3102 does nothave a hard disk. In one aspect, a client device 3102 has a displaysmaller than a display supported by a server 3106. In one aspect, aclient device may include one or more client devices.

In some embodiments, a server 3106 may represent a computer, a laptopcomputer, a computing device, a virtual machine (e.g., VMware® VirtualMachine), a desktop session (e.g., Microsoft Terminal Server), apublished application (e.g., Microsoft Terminal Server) or a suitabledevice with a processor. In some embodiments, a server 3106 can bestationary. In some embodiments, a server 3106 can be mobile. In certainconfigurations, a server 3106 may be any device that can represent aclient device. In some embodiments, a server 3106 may include one ormore servers.

In one example, a first device is remote to a second device when thefirst device is not directly connected to the second device. In oneexample, a first remote device may be connected to a second device overa communication network such as a Local Area Network (LAN), a Wide AreaNetwork (WAN), and/or other network.

When a client device 3102 and a server 3106 are remote with respect toeach other, a client device 3102 may connect to a server 3106 over anetwork 3104, for example, via a modem connection, a LAN connectionincluding the Ethernet or a broadband WAN connection including DSL,Cable, T1, T3, Fiber Optics, Wi-Fi, or a mobile network connectionincluding GSM, GPRS, 3G, WiMax or other network connection. A network3104 can be a LAN network, a WAN network, a wireless network, theInternet, an intranet or other network. A network 3104 may include oneor more routers for routing data between client devices and/or servers.A remote device (e.g., client device, server) on a network may beaddressed by a corresponding network address, such as, but not limitedto, an Internet protocol (IP) address, an Internet name, a WindowsInternet name service (WINS) name, a domain name or other system name.These illustrate some examples as to how one device may be remote toanother device. But the subject technology is not limited to theseexamples.

According to certain embodiments of the subject technology, the terms“server” and “remote server” are generally used synonymously in relationto a client device, and the word “remote” may indicate that a server isin communication with other device(s), for example, over a networkconnection(s).

According to certain embodiments of the subject technology, the terms“client device” and “remote client device” are generally usedsynonymously in relation to a server, and the word “remote” may indicatethat a client device is in communication with a server(s), for example,over a network connection(s).

In some embodiments, a “client device” may be sometimes referred to as aclient or vice versa. Similarly, a “server” may be sometimes referred toas a server device or vice versa.

In some embodiments, the terms “local” and “remote” are relative terms,and a client device may be referred to as a local client device or aremote client device, depending on whether a client device is describedfrom a client side or from a server side, respectively. Similarly, aserver may be referred to as a local server or a remote server,depending on whether a server is described from a server side or from aclient side, respectively. Furthermore, an application running on aserver may be referred to as a local application, if described from aserver side, and may be referred to as a remote application, ifdescribed from a client side.

In some embodiments, devices placed on a client side (e.g., devicesconnected directly to a client device(s) or to one another using wiresor wirelessly) may be referred to as local devices with respect to aclient device and remote devices with respect to a server. Similarly,devices placed on a server side (e.g., devices connected directly to aserver(s) or to one another using wires or wirelessly) may be referredto as local devices with respect to a server and remote devices withrespect to a client device.

As used herein, the word “module” refers to logic embodied in hardwareor firmware, or to a collection of software instructions, possiblyhaving entry and exit points, written in a programming language, suchas, for example C++. A software module may be compiled and linked intoan executable program, installed in a dynamic link library, or may bewritten in an interpretive language such as BASIC. It will beappreciated that software modules may be callable from other modules orfrom themselves, and/or may be invoked in response to detected events orinterrupts. Software instructions may be embedded in firmware, such asan EPROM or EEPROM. It will be further appreciated that hardware modulesmay be comprised of connected logic units, such as gates and flip-flops,and/or may be comprised of programmable units, such as programmable gatearrays or processors. The modules described herein are preferablyimplemented as software modules, but may be represented in hardware orfirmware.

It is contemplated that the modules may be integrated into a fewernumber of modules. One module may also be separated into multiplemodules. The described modules may be implemented as hardware, software,firmware or any combination thereof. Additionally, the described modulesmay reside at different locations connected through a wired or wirelessnetwork, or the Internet.

In general, it will be appreciated that the processors can include, byway of example, computers, program logic, or other substrateconfigurations representing data and instructions, which operate asdescribed herein. In other embodiments, the processors can includecontroller circuitry, processor circuitry, processors, general purposesingle-chip or multi-chip microprocessors, digital signal processors,embedded microprocessors, microcontrollers and the like.

Furthermore, it will be appreciated that in one embodiment, the programlogic may advantageously be implemented as one or more components. Thecomponents may advantageously be configured to execute on one or moreprocessors. The components include, but are not limited to, software orhardware components, modules such as software modules, object-orientedsoftware components, class components and task components, processesmethods, functions, attributes, procedures, subroutines, segments ofprogram code, drivers, firmware, microcode, circuitry, data, databases,data structures, tables, arrays, and variables.

The foregoing description is provided to enable a person skilled in theart to practice the various configurations described herein. While thesubject technology has been particularly described with reference to thevarious figures and configurations, it should be understood that theseare for illustration purposes only and should not be taken as limitingthe scope of the subject technology.

There may be many other ways to implement the subject technology.Various functions and elements described herein may be partitioneddifferently from those shown without departing from the scope of thesubject technology. Various modifications to these configurations willbe readily apparent to those skilled in the art, and generic principlesdefined herein may be applied to other configurations. Thus, manychanges and modifications may be made to the subject technology, by onehaving ordinary skill in the art, without departing from the scope ofthe subject technology.

It is understood that the specific order or hierarchy of steps in theprocesses disclosed is an illustration of exemplary approaches. Basedupon design preferences, it is understood that the specific order orhierarchy of steps in the processes may be rearranged. Some of the stepsmay be performed simultaneously. The accompanying method claims presentelements of the various steps in a sample order, and are not meant to belimited to the specific order or hierarchy presented.

As used herein, the phrase “at least one of” preceding a series ofitems, with the term “and” or “or” to separate any of the items,modifies the list as a whole, rather than each member of the list (i.e.,each item). The phrase “at least one of” does not require selection ofat least one of each item listed; rather, the phrase allows a meaningthat includes at least one of any one of the items, and/or at least oneof any combination of the items, and/or at least one of each of theitems. By way of example, the phrases “at least one of A, B, and C” or“at least one of A, B, or C” each refer to only A, only B, or only C;any combination of A, B, and C; and/or at least one of each of A, B, andC.

Terms such as “top,” “bottom,” “front,” “rear” and the like as used inthis disclosure should be understood as referring to an arbitrary frameof reference, father than to the ordinary gravitational frame ofreference. Thus, a top surface, a bottom surface, a front surface, and arear surface may extend upwardly, downwardly, diagonally, orhorizontally in a gravitational frame of reference.

Furthermore, to the extent that the term “include,” “have,” or the likeis used in the description or the claims, such term is intended to beinclusive in a manner similar to the term “comprise” as “comprise” isinterpreted when employed as a transitional word in a claim.

The word “exemplary” is used herein to mean “serving as an example,instance, or illustration.” Any embodiment described herein as“exemplary” is not necessarily to be construed as preferred oradvantageous over other embodiments.

A reference to an element in the singular is not intended to mean “oneand only one” unless specifically stated, but rather “one or more.”Pronouns in the masculine (e.g., his) include the feminine and neutergender (e.g., her and its) and vice versa. The term “some” refers to oneor more. Underlined and/or italicized headings and subheadings are usedfor convenience only, do not limit the subject technology, and are notreferred to in connection with the interpretation of the description ofthe subject technology. All structural and functional equivalents to theelements of the various configurations described throughout thisdisclosure that are known or later come to be known to those of ordinaryskill in the art are expressly incorporated herein by reference andintended to be encompassed by the subject technology. Moreover, nothingdisclosed herein is intended to be dedicated to the public regardless ofwhether such disclosure is explicitly recited in the above description.

While certain aspects and embodiments of the invention have beendescribed, these have been presented by way of example only, and are notintended to limit the scope of the invention. Indeed, the novel methodsand systems described herein may be embodied in a variety of other formswithout departing from the spirit thereof. The accompanying claims andtheir equivalents are intended to cover such forms or modifications aswould fall within the scope and spirit of the invention.

What is claimed is:
 1. A computed tomography device, comprising: agantry configured to rotate about an axis and comprising an openingconfigured to accommodate an object; an x-ray radiation source mountedto the gantry to produce an x-ray radiation; a collimator positionedbetween the x-ray radiation source and the gantry opening, thecollimator comprising first and second leaves respectively boundingfirst and second opposing sides of an x-ray radiation delivery window,the first leaf and the second leaf being independently movable to adjustat least one of a size or a location of the x-ray radiation deliverywindow relative to the x-ray radiation source in a directionnon-parallel to the axis, and wherein the first leaf is movableindependently of the second leaf so as to form a collimated radiationwhich is dynamically coordinated with a region of interest (ROI) withinthe object during a scan; and a collimator controller operativelyconnected to the collimator and adapted to independently controlmovement of the first and second leaves as transverse collimatorsaccording to Equations (1)-(3): $\begin{matrix}{{Q(t)} = {C \cdot {\tan\left( {{\arcsin\left( \frac{R_{1}}{L(t)} \right)} + {\arcsin\left( {\frac{R_{0}}{L(t)} \cdot {\sin\left( {{\theta(t)} - \theta_{0}} \right)}} \right)}} \right)}}} & (1) \\{{L(t)} = \sqrt{\left( {S \cdot {\sin\left( {{\theta(t)} - \theta_{0}} \right)}} \right)^{2} + \left( {{S \cdot {\cos\left( {{\theta(t)} - \theta_{0}} \right)}} - R_{0}} \right)^{2}}} & (2) \\{{\frac{\partial{Q(t)}}{\partial t} \approx {Q^{\prime}(t)}} = {\frac{C \cdot \pi \cdot R_{0}}{\rho \cdot S} \cdot \frac{\left( {{\cos\left( {{\theta(t)} - \theta_{0}} \right)} - {\frac{R_{1}}{S} \cdot {\sin\left( {{\theta(t)} - \theta_{0}} \right)}} - \frac{R_{0}}{S}} \right)}{\left( {1 - {\frac{R_{0}}{S} \cdot {\cos\left( {{\theta(t)} - \theta_{0}} \right)}}} \right)^{2}}}} & (3)\end{matrix}$  where Q(t) is a transverse collimator leaf position,Q′(t) is an approximate leaf velocity, rotation speed is ρ, collimatordistance C, distance S from an ideal radiation point source to a scanisocenter, ROI radius R₁, offset R₀ at angle θ₀, and L(t) is a distancefrom an ideal radiation point source to a center of the ROI.
 2. Thecomputed tomography device of claim 1, the collimator further comprisingthird and fourth leaves respectively bounding third and fourth opposingsides of the x-ray radiation delivery window and aligned with the x-rayradiation delivery window along the axis.
 3. The computed tomographydevice of claim 2, wherein each of the first and second sides issubstantially orthogonal to each of the third and fourth sides and thecollimator is further adapted to independently control the third andfourth leaves as axial collimators according to Equations (4) and (5):$\begin{matrix}{{{{H(t)} > 0}:{Q(t)}} = {{{\frac{C \cdot w}{2 \cdot S} \cdot \left( {1 + \frac{2 \cdot P \cdot t}{\rho \cdot \left( {1 + \frac{R}{S}} \right)}} \right)}\frac{\partial{Q(t)}}{\partial t}} = \frac{C \cdot w \cdot P}{\rho \cdot \left( {S + R} \right)}}} & (4) \\{{{{H(t)} < 0}:{Q(t)}} = {{{\frac{C \cdot w}{2 \cdot S} \cdot \left( {1 + \frac{2 \cdot P \cdot t}{\rho \cdot \left( {1 - \frac{R}{S}} \right)}} \right)}\frac{\partial{Q(t)}}{\partial t}} = \frac{C \cdot w \cdot P}{\rho \cdot \left( {S - R} \right)}}} & (5)\end{matrix}$ where axial collimator position is Q(t), velocity isδQ/δt, P is helical pitch, helical position H(t), rotation speed ρ,detector width w, collimator distance C, point source to isocenterdistance S, and cylindrical VOI radius R.
 4. The computed tomographydevice of claim 1, wherein the collimator is mounted within about 27 cmof the x-ray radiation source.
 5. The computed tomography device ofclaim 1, wherein the collimator is mounted within about 12 cm of thex-ray radiation source.
 6. The computed tomography device of claim 1,wherein the first leaf and the second leaf are independently movablerelative to the x-ray radiation source in a direction tangential to acircle (i) centered on the axis and (i) defining a plane that is notparallel to the axis.
 7. A method of radiologic imaging, comprising:rotating, about an axis, a gantry carrying an x-ray radiation source;emitting x-ray radiation from the x-ray radiation source toward anobject between a pair of independently movable transverse collimatingleaves; during rotation of the gantry, moving the pair of collimatingleaves relative to the x-ray radiation source in a direction nonparallelto the axis to form a collimated radiation which is dynamicallycoordinated with a region of interest (ROI) within the object during ascan, wherein the moving controls movement of the pair of leavesaccording to Equations (1)-(3): $\begin{matrix}{{Q(t)} = {C \cdot {\tan\left( {{\arcsin\left( \frac{R_{1}}{L(t)} \right)} + {\arcsin\left( {\frac{R_{0}}{L(t)} \cdot {\sin\left( {{\theta(t)} - \theta_{0}} \right)}} \right)}} \right)}}} & (1) \\{{L(t)} = \sqrt{\left( {S \cdot {\sin\left( {{\theta(t)} - \theta_{0}} \right)}} \right)^{2} + \left( {{S \cdot {\cos\left( {{\theta(t)} - \theta_{0}} \right)}} - R_{0}} \right)^{2}}} & (2) \\{{\frac{\partial{Q(t)}}{\partial t} \approx {Q^{\prime}(t)}} = {\frac{C \cdot \pi \cdot R_{0}}{\rho \cdot S} \cdot \frac{\left( {{\cos\left( {{\theta(t)} - \theta_{0}} \right)} - {\frac{R_{1}}{S} \cdot {\sin\left( {{\theta(t)} - \theta_{0}} \right)}} - \frac{R_{0}}{S}} \right)}{\left( {1 - {\frac{R_{0}}{S} \cdot {\cos\left( {{\theta(t)} - \theta_{0}} \right)}}} \right)^{2}}}} & (3)\end{matrix}$  where Q(t) is a transverse collimator leaf position,Q′(t) is an approximate leaf velocity, rotation speed is ρ, collimatordistance C, distance S from an ideal radiation point source to a scanisocenter, ROI radius R₁, offset R₀ at angle θ₀, and L(t) is a distancefrom an ideal radiation point source to a center of the ROI.
 8. Themethod of claim 7, further comprising: performing a preliminary scan ofan object; demarcating a region of interest in the object, based on thepreliminary scan, that is at least one of (i) non-concentric with theaxis or (ii) non-circular; and controlling movement of the pair ofleaves during rotation of the gantry to adjust at least one of alocation, relative to the x-ray radiation source, or a dimension, of anx-ray radiation delivery window such that substantially only the regionof interest is exposed to x-ray radiation through the x-ray radiationdelivery window.
 9. The method of claim 8, further comprising directingx-ray radiation through a plurality of secondary windows, on opposingsides of the x-ray radiation delivery window, to regions in the objectoutside the region of interest; and substantially blocking the passageof x-ray radiation toward the object in regions between the x-rayradiation delivery window and the secondary windows.
 10. The method ofclaim 7, further comprising repositioning the object such that a regionof interest is located closer to the axis.
 11. The method of claim 7,the emitting x-ray radiation further includes directing the x-rayradiation between a pair of independently movable axial collimatingleaves which are movable in a direction parallel to the axis and themethod further comprises, during rotation of the gantry, moving the pairof independently movable axial collimating leaves according to Equations(4) and (5): $\begin{matrix}{{{{H(t)} > 0}:{Q(t)}} = {{{\frac{C \cdot w}{2 \cdot S} \cdot \left( {1 + \frac{2 \cdot P \cdot t}{\rho \cdot \left( {1 + \frac{R}{S}} \right)}} \right)}\frac{\partial{Q(t)}}{\partial t}} = \frac{C \cdot w \cdot P}{\rho \cdot \left( {S + R} \right)}}} & (4) \\{{{{H(t)} < 0}:{Q(t)}} = {{{\frac{C \cdot w}{2 \cdot S} \cdot \left( {1 + \frac{2 \cdot P \cdot t}{\rho \cdot \left( {1 - \frac{R}{S}} \right)}} \right)}\frac{\partial{Q(t)}}{\partial t}} = \frac{C \cdot w \cdot P}{\rho \cdot \left( {S - R} \right)}}} & (5)\end{matrix}$ where axial collimator position is Q(t), velocity isδQ/δt, P is helical pitch, helical position H(t), rotation speed ρ,detector width w, collimator distance C, point source to isocenterdistance S, and cylindrical VOI radius R.